US9833561B2 - Occlusion detection in delivery of fluids - Google Patents

Occlusion detection in delivery of fluids Download PDF

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US9833561B2
US9833561B2 US14/655,182 US201314655182A US9833561B2 US 9833561 B2 US9833561 B2 US 9833561B2 US 201314655182 A US201314655182 A US 201314655182A US 9833561 B2 US9833561 B2 US 9833561B2
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force
perturbation
fluid flow
perturbed
occlusion
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US20150374902A1 (en
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Joshua Chambers
John O'Mahony
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Gambro Lundia AB
Nuwellis Inc
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Gambro Lundia AB
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
    • A61M5/14—Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
    • A61M5/142—Pressure infusion, e.g. using pumps
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
    • A61M1/36—Other treatment of blood in a by-pass of the natural circulatory system, e.g. temperature adaptation, irradiation ; Extra-corporeal blood circuits
    • A61M1/3672—Means preventing coagulation
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
    • A61M5/14—Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
    • A61M5/168—Means for controlling media flow to the body or for metering media to the body, e.g. drip meters, counters ; Monitoring media flow to the body
    • A61M5/16831—Monitoring, detecting, signalling or eliminating infusion flow anomalies
    • A61M5/16854—Monitoring, detecting, signalling or eliminating infusion flow anomalies by monitoring line pressure
    • A61M5/16859—Evaluation of pressure response, e.g. to an applied pulse
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
    • A61M5/14—Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
    • A61M5/168—Means for controlling media flow to the body or for metering media to the body, e.g. drip meters, counters ; Monitoring media flow to the body
    • A61M5/172—Means for controlling media flow to the body or for metering media to the body, e.g. drip meters, counters ; Monitoring media flow to the body electrical or electronic
    • F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
    • F04—POSITIVE - DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS FOR LIQUIDS OR ELASTIC FLUIDS
    • F04B—POSITIVE-DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS
    • F04B51/00—Testing machines, pumps, or pumping installations
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
    • A61M1/36—Other treatment of blood in a by-pass of the natural circulatory system, e.g. temperature adaptation, irradiation ; Extra-corporeal blood circuits
    • A61M1/3672—Means preventing coagulation
    • A61M1/3673—Anticoagulant coating, e.g. Heparin coating
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
    • A61M5/14—Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
    • A61M5/168—Means for controlling media flow to the body or for metering media to the body, e.g. drip meters, counters ; Monitoring media flow to the body
    • A61M5/16831—Monitoring, detecting, signalling or eliminating infusion flow anomalies
    • A61M2005/16863—Occlusion detection
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M2205/00—General characteristics of the apparatus
    • A61M2205/18—General characteristics of the apparatus with alarm
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M2205/00—General characteristics of the apparatus
    • A61M2205/33—Controlling, regulating or measuring
    • A61M2205/332—Force measuring means
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M2209/00—Ancillary equipment
    • A61M2209/02—Equipment for testing the apparatus
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
    • A61M5/14—Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
    • A61M5/168—Means for controlling media flow to the body or for metering media to the body, e.g. drip meters, counters ; Monitoring media flow to the body
    • A61M5/16831—Monitoring, detecting, signalling or eliminating infusion flow anomalies
    • A61M5/16854—Monitoring, detecting, signalling or eliminating infusion flow anomalies by monitoring line pressure

Definitions

  • the disclosure herein relates to monitoring delivery of fluids from, for example, a fluid delivery system (e.g., an infusion pump, such as a syringe pump). More particularly, the disclosure relates to detection of an abnormality in the delivery of such fluids (e.g., fluid flow occlusion due, for example, to an obstructed line in the fluid delivery system).
  • a fluid delivery system e.g., an infusion pump, such as a syringe pump.
  • an abnormality in the delivery of such fluids e.g., fluid flow occlusion due, for example, to an obstructed line in the fluid delivery system.
  • Infusion devices are used for the delivery of medical fluids in various situations, e.g., such as the delivery of medical fluids for an extracorporeal blood circuit, drug infusion, etc.
  • infusion devices may be usefully applied for infusing an anticoagulant in an extracorporeal circuit operatively associated with a machine for extracorporeal blood treatment.
  • extracorporeal treatments may include removal of blood from the patient, external treatment thereof away from the human body, followed by its return to the patient.
  • extracorporeal blood may be made to circulate through a circuit comprising, in general, an arterial line, or blood removal line, which takes the blood from the patient to a blood treatment device (e.g., a dialyzer filter) and a venous line, or blood return line, which returns the treated blood to the patient.
  • a blood treatment device e.g., a dialyzer filter
  • a venous line, or blood return line which returns the treated blood to the patient.
  • an anticoagulant e.g., heparin
  • An infusion device that may be used, for example, to deliver the anticoagulant may include a syringe pump.
  • the syringe pump may include a pushing element, operable on command of a linear actuator, to push a plunger of the syringe containing the anticoagulant at an advancement rate which is predetermined (e.g., relatively slow).
  • the syringe may contain a quantity of anticoagulant necessary for several hours of treatment.
  • the pushing element and the actuator may be part of the extracorporeal treatment machine (e.g., a dialysis machine), while the syringe may be of the single-use type (e.g., of the disposable type).
  • Such extracorporeal treatment machines or systems, as well as other apparatus that employ infusion devices may also include monitoring techniques relating to the occurrence of overpressures developing internally in the syringe (e.g., pressures due, for example, to occlusions in the infusion line, with a consequent interruption in the infusion flow).
  • monitoring techniques relating to the occurrence of overpressures developing internally in the syringe (e.g., pressures due, for example, to occlusions in the infusion line, with a consequent interruption in the infusion flow).
  • the delay between the occurrence of an occlusion and its detection, as well as, for example, the provision of an alarm associated with such detection is relevant in terms of patient safety.
  • clinical practices teach that a loss of anticoagulant infusion for more than fifteen minutes may cause the formation of blood clots in the extracorporeal circuit which, if not quickly identified, may become nuclei of bigger and progressively-growing clots.
  • U.S. Pat. No. 5,295,967 to Rondelet et al. entitled “Syringe Pump Having Continuous Pressure Monitoring and Display”, describes a syringe pump that includes a force transducer for continuously monitoring the force on the syringe plunger, a microprocessor for converting the measured force into a syringe pressure reading, and a display on which the syringe pressure continuously appears in order for the syringe pressure to be monitored during pumping.
  • U.S. Pat. No. 5,087,245 to Doan entitled “System and Method for Detecting Abnormalities in Intravascular Infusion”
  • systems and methods to detect occlusions by producing perturbations of fluid flow by varying the flow rate of the fluid with respect to an equilibrium flow rate, measuring a pressure level of the fluid over a period of time to determine equilibrium pressure and a pressure response of the fluid to the perturbation, determining a first integral of the difference between the equilibrium pressure and the pressure response, determining resistance to fluid flow based on the integral, determining a second integral of the product of time and the difference between the pressure response and equilibrium pressure, and determining a compliance value by dividing the second integral by the first integral.
  • Such resistance and compliance values are displayed, and an alarm is generated when the resistance or compliance parameters fall outside of reference ranges.
  • the present disclosure describes systems, methods, and apparatus which may be used to detect abnormalities in delivery of a fluid, for example, from an infusion apparatus (e.g., a syringe pump).
  • an infusion apparatus e.g., a syringe pump
  • the detection of such abnormalities in the delivery of the fluid is capable of accommodating a wide range of delivery or infusion apparatus (e.g., wide range of syringe pumps), even in view of such infusion apparatus compliances, resistances, and inconsistencies (e.g., the detection algorithm uses a normalized quantity or ratio that is relatively independent of such characteristics).
  • the ratio used e.g., a normalized area ratio value; where the normalization is based on a measured maximum perturbation force
  • the ratio used is fundamentally invariant to a wide variety of changes in syringe pump parameters and system configurations, while still being extremely sensitive to the increased flow resistance indicative of an occlusion.
  • one or more embodiments provided herein may provide occlusion detection functionality that allows a machine or apparatus for extracorporeal blood treatment to protect against undesired absence of infusion, even in cases of very low infusion flow rates, by signaling (e.g., in a reasonable time frame) a danger of occlusion in the infusion flow.
  • a machine or apparatus may provide occlusion detection which may signal (e.g., in a reasonable time frame) the occurrence of a situation which can be linked to an insufficient infusion flow and/or an overpressure.
  • the system may include an infusion apparatus (e.g., a syringe pump) controllable to provide a fluid flow at an infusion flow rate and wherein the infusion apparatus is further controllable to intermittently deliver a defined volume of fluid resulting in one or more perturbations in the fluid flow.
  • an infusion apparatus e.g., a syringe pump
  • the infusion apparatus is further controllable to intermittently deliver a defined volume of fluid resulting in one or more perturbations in the fluid flow.
  • the system may also include a force transducer configured to measure a perturbed force response over time resulting from each of the one or more perturbations (e.g., a force sensor, such as, a load cell associated with an actuator used to control actuation of the syringe pump) and a controller configured to control the infusion apparatus to provide a fluid flow at an infusion flow rate and to cause one or more perturbations in the fluid flow (e.g., each of the one or more perturbations in the fluid flow result in a measurable perturbed force response).
  • a force transducer configured to measure a perturbed force response over time resulting from each of the one or more perturbations
  • a force transducer configured to measure a perturbed force response over time resulting from each of the one or more perturbations
  • a force transducer configured to measure a perturbed force response over time resulting from each of the one or more perturbations
  • a force transducer configured to measure a perturbed force response over time resulting from each of
  • the controller may further be configured to receive a force signal representative of a perturbed force response including at least a maximum perturbation force resulting from at least one perturbation caused in the fluid flow, determine an integrated perturbed force response value using integration of the force signal over a perturbation time period (e.g., the integrated perturbed force response value being representative of an additional force caused by the at least one perturbation over an equilibrium force), provide a ratio corresponding to the at least one perturbation between the integrated perturbed force response value and a normalizing value (e.g., wherein the normalizing value is based at least on the maximum perturbation force), and determine if fluid flow is occluded based at least on the ratio corresponding to the at least one perturbation.
  • a force signal representative of a perturbed force response including at least a maximum perturbation force resulting from at least one perturbation caused in the fluid flow
  • determine an integrated perturbed force response value using integration of the force signal over a perturbation time period e.g., the integrated perturbed force response value
  • the method may include providing a fluid flow at an infusion flow rate, intermittently delivering a defined volume of fluid causing at least one perturbation in the fluid flow (e.g., wherein the at least one perturbation in the fluid flow results in a perturbed force response over time), measuring the perturbed force response including at least a maximum perturbation force resulting from the at least one perturbation caused in the fluid flow and generating a force signal representative thereof, determining an integrated perturbed force response value using integration of the force signal over a perturbation time period (e.g., the integrated perturbed force response value being representative of an additional force caused by the at least one perturbation over an equilibrium force), and providing a ratio corresponding to the at least one perturbation between the integrated perturbed force response value and a normalizing value (e.g., wherein the normalizing value is based at least on the maximum perturbation force).
  • a perturbation time period e.g., the integrated perturbed force response value being representative of an additional force caused by the at least one perturbation over an
  • the apparatus may include an extracorporeal blood circuit, a syringe pump controllable to provide a fluid flow into the extracorporeal blood circuit at an infusion flow rate (e.g., a fluid flow that includes an anticoagulant) and further controllable to intermittently deliver a defined volume of fluid resulting in one or more perturbations in the fluid flow, a force transducer configured to measure a perturbed force response over time resulting from each of the one or more perturbations, and a controller configured to control the syringe pump to provide a fluid flow at an infusion flow rate and to cause one or more perturbations in the fluid flow (e.g., wherein each of the one or more perturbations in the fluid flow result in a measurable perturbed force response).
  • an infusion flow rate e.g., a fluid flow that includes an anticoagulant
  • a force transducer configured to measure a perturbed force response over time resulting from each of the one or more perturbations
  • a controller configured to control the sy
  • the controller may further be configured to receive a force signal representative of a perturbed force response including at least a maximum perturbation force resulting from at least one perturbation caused in the fluid flow, determine an integrated perturbed force response value using integration of the force signal over a perturbation time period (e.g., the integrated perturbed force response value being representative of an additional force caused by the at least one perturbation over an equilibrium force), provide a ratio corresponding to the at least one perturbation between the integrated perturbed force response value and a normalizing value (e.g., wherein the normalizing value is based at least on the maximum perturbation force), and determine if fluid flow is occluded based at least on the ratio corresponding to the at least one perturbation.
  • a force signal representative of a perturbed force response including at least a maximum perturbation force resulting from at least one perturbation caused in the fluid flow
  • determine an integrated perturbed force response value using integration of the force signal over a perturbation time period e.g., the integrated perturbed force response value
  • determining if fluid flow is occluded based at least on the ratio corresponding to the at least one perturbation may include comparing the ratio to a predetermined ratio indicative of an occlusion.
  • the integrated perturbed force response value may be representative of an integration, taken over the perturbation time period, of the force signal representative of the perturbed force response taking into consideration the equilibrium force (e.g., the integration may be initiated at the maximum perturbation force).
  • the normalizing value may be representative of an integration, taken over the perturbation time period, of the maximum perturbation force relative to equilibrium force (e.g., the integration may be initiated at the maximum perturbation force).
  • the normalizing value may be representative of an integration, over the perturbation time period, of the force signal representative of the perturbed force response relative to the maximum force signal (e.g., the integration may be initiated at the maximum perturbation force).
  • the integrated perturbed force response value may be representative of an integration, over the perturbation time period, of the force signal representative of the perturbed force response relative to the maximum force signal (e.g., the integration may be initiated at the maximum perturbation force).
  • the normalizing value may be representative of an integration, taken over the perturbation time period, of the maximum perturbation force relative to equilibrium force (e.g., the integration may be initiated at the maximum perturbation force).
  • the normalizing value may be determined based on the perturbed force response of the fluid flow as if a substantially total occlusion were present, an alarm may be configured to be activated upon determination of an occluded fluid flow, the infusion apparatus may include a syringe pump, the infusion apparatus may be configured to infuse an anticoagulant into an extracorporeal blood circuit, and/or the detection techniques may be used in an apparatus for extracorporeal blood treatment.
  • FIG. 1 is a simplified block diagram of an exemplary fluid delivery system for detecting abnormalities in the delivery of fluids by an infusion apparatus.
  • FIG. 2 is an illustration of an exemplary infusion apparatus such as shown generally in FIG. 1 .
  • FIG. 3 is block diagram illustrating an exemplary algorithm for detecting abnormalities in delivery of a fluid by an infusion apparatus which may be implemented by a system, for example, such as shown generally in FIG. 1 .
  • FIG. 4 is a graphical illustration of an exemplary perturbed force response for use in describing the exemplary algorithm shown generally in FIG. 3 .
  • FIG. 5 is a block diagram illustrating another exemplary algorithm for use in detecting abnormalities in delivery of a fluid by an infusion apparatus which may be implemented by a system, for example, such as shown generally in FIG. 1 .
  • FIG. 6 is a perspective view of an exemplary extracorporeal blood treatment apparatus or machine that may include and/or implement the detection and monitoring functionality described herein.
  • FIGS. 7-10 show various graphical illustrations for use in describing one of more exemplary embodiments of the implementation of one or more algorithms described herein.
  • Exemplary systems, methods, and apparatus for use in the monitoring and/or detection of abnormalities and/or occlusion of fluid flow being delivered by infusion apparatus shall be described with reference to FIGS. 1-10 .
  • one or more embodiments of such systems, apparatus, and methods may use the pressure of the fluid being infused (e.g., measured directly or indirectly; for example, indirectly measured using a force sensor associated with the infusion apparatus) to detect an abnormality within the fluid flow, for example, such as an occlusion.
  • the terms force and pressure shall be used interchangeable herein.
  • the fluid being injected or infused may be periodically perturbed such that the pressure in the fluid (e.g., which may be represented by a force measurement associated with the infusion apparatus used to provide the perturbation) changes between a perturbed value an equilibrium value.
  • Perturbation is typically a short term increase in the infusion rate of the fluid which in turn causes a momentary increase in the pressure in the fluid. This momentary increase in pressure decreases back to equilibrium value over some period of time.
  • a perturbation force response or pressure response
  • the perturbation force response In normal, as opposed to abnormal, infusion operation (e.g., with no partial or total occlusion present), the perturbation force response generally includes a maximum perturbation force or pressure reached shortly after the perturbation of the fluid flow followed by a rate of decay in the perturbation force response back to an equilibrium value (see, e.g., FIG. 4 ).
  • a maximum perturbation pressure will also be reached shortly after perturbation of the fluid flow, however, the rate of decay of the perturbation force response back to an equilibrium value will be different than in normal operation (e.g., the rate of decay may be much slower or even non-existent in the cases of a complete occlusion).
  • the differences in the perturbation force response for normal versus abnormal operation can be used as described herein to provide detection of abnormalities in fluid flow provided by an infusion apparatus.
  • a value may be obtained related to the maximum perturbation force and the rate of decay of the perturbation.
  • a ratio e.g., an area ratio
  • the ratio related substantially only to the rate of decay of the perturbation is directly related to the flow resistance of the infusion apparatus, the ratio provides an indicator of high resistance or occlusive situations in the infusion circuit.
  • certain combinations of low flow rate conditions and poor infusion device performance can result in momentarily giving the appearance of occlusivity without abnormal operation or true line occlusion being present.
  • This type of noise can be taken into consideration and rejected by examining subsequent ratios (e.g., area ratios) determined for one or more subsequent perturbations provided in the fluid flow, and, thereafter, alarming, or otherwise indicating an abnormal or occlusive condition, only after a certain number of ratios have indicated such a condition.
  • the sensitivity of the ratio technique combined with the calculation of ratios for multiple perturbations results in a highly robust and fast detection of abnormal conditions such that an alarm may be provided in a reasonable time frame.
  • various parameters may be adjusted to optimize the implementation of the detection functionality.
  • the amount of time to integrate e.g., upon detection of the maximum perturbation force in the perturbation force response
  • the ratios used as thresholds which indicate an occlusion or abnormal condition e.g., the magnitude of such ratios
  • the number of ratios in a row corresponding to perturbations indicative of an occlusive condition necessary to determine that an abnormal condition or occlusive condition exists e.g., to de-noise the detection functionality and, for example, prevent a single ratio from triggering an alarm when line occlusion is not actually present
  • the amount of time to integrate e.g., upon detection of the maximum perturbation force in the perturbation force response
  • the ratios used as thresholds which indicate an occlusion or abnormal condition e.g., the magnitude of such ratios
  • the number of ratios in a row corresponding to perturbations indicative of an occlusive condition necessary to determine that an abnormal condition or occlusive condition exists e.g.,
  • Such adjustability can be used to accommodate a wide range of infusion device compliances, resistances and inconsistencies. Further, because the ratio used is a normalized quantity, it is relatively independent of infusion device characteristics; which greatly simplifies the determination of such parameters suitable to provide effective occlusion detection.
  • FIG. 1 shows one general exemplary embodiment of a fluid delivery system 10 including an occlusion monitoring system 20 for use in monitoring and detecting abnormalities in a fluid flow provided by an infusion apparatus 12 (e.g., a flow of fluid from a fluid reservoir 16 delivered by an infusion pump 15 , or other infusion apparatus, into a line 13 of a circuit, for example, such as delivery of fluid in small boluses into a line of an extracorporeal blood circuit of an extracorporeal blood treatment apparatus, such as generally shown in FIG. 6 ).
  • an infusion apparatus 12 e.g., a flow of fluid from a fluid reservoir 16 delivered by an infusion pump 15 , or other infusion apparatus, into a line 13 of a circuit, for example, such as delivery of fluid in small boluses into a line of an extracorporeal blood circuit of an extracorporeal blood treatment apparatus, such as generally shown in FIG. 6 ).
  • the fluid flow may be delivered by the infusion apparatus 12 under control of controller 14 provided with an input from force sensor 18 (e.g., via an analog to digital (A/D) converter 21 ), as well as other control inputs (e.g., such as displacement sensors of an actuator for the infusion apparatus, etc.).
  • the controller 14 is associated with memory 22 for use in carrying out the functionality as described herein.
  • the monitoring system 20 may include an alarm 24 for providing an alarm indication when an abnormal condition or occlusion is detected.
  • the system 10 includes infusion apparatus 12 (e.g., a syringe pump) which under control of controller 14 may provide a fluid flow at an infusion flow rate (e.g., using an infusion pattern to control the pump to deliver small boluses).
  • the infusion apparatus 12 is associated with a force sensor 18 configured to provide a force signal to controller 14 representative of the fluid flow being delivered by infusion apparatus 12 .
  • the controller 14 is further configured to control the infusion apparatus 12 to intermittently deliver a defined volume of fluid resulting in one or more perturbations in the fluid flow (e.g., a drive system of the syringe pump may be actuated to move the syringe plunger in small steps; each step producing a small bolus infusion into an infusion line).
  • a drive system of the syringe pump may be actuated to move the syringe plunger in small steps; each step producing a small bolus infusion into an infusion line.
  • Each of such perturbations in the fluid flow may result in a measurable perturbed force response (e.g., measurable over time by force sensor 18 ).
  • the resulting measurable perturbed force response includes at least a maximum perturbation force resulting from the perturbation caused in the fluid flow.
  • the controller 14 is further configured to determine an integrated perturbed force response value using integration of the force signal over a perturbation time period (e.g., a predetermined or set time period following a perturbation).
  • the integrated perturbed force response value is representative of an additional force caused by the at least one perturbation over an equilibrium force.
  • the integrated perturbed force response value may be representative of area A 1 or area A 2 .
  • the controller 14 is configured to provide a ratio corresponding to the perturbation between the integrated perturbed force response value and a normalizing value. The normalizing value is based at least on the maximum perturbation force of the measured perturbed force response.
  • the normalizing value may be representative of area A 2 or area (A 1 +A 2 ).
  • the controller 14 may determine if fluid flow is occluded. For example, it may be determined that fluid flow is occluded based on a comparison of the ratio corresponding to each of one or more perturbations to a predetermined ratio indicative of an occlusion (e.g., a threshold ratio that indicates an occlusion is present).
  • the infusion apparatus 12 may be any suitable apparatus for delivering a fluid flow.
  • such infusion apparatus may include a syringe pump, such as, for example, described herein, a peristaltic pump, patient controlled pumps (e.g., patient controlled analgesia (PCA) pumps, intravenous (IV) pumps (e.g., using a pressure measured in the line after the drip), etc.
  • PCA patient controlled analgesia
  • IV intravenous
  • FIG. 2 One exemplary infusion apparatus 36 (e.g., a syringe pump) is shown in FIG. 2 .
  • the exemplary infusion apparatus 36 may be disposed on a housing such as shown generally by the reference numeral 55 (e.g., mounted on a panel of a machine or apparatus such as shown in FIG. 6 ).
  • the housing 55 may be configured to receive a syringe 40 containing a fluid to be delivered thereby (e.g., an anticoagulant to be delivered into an extracorporeal blood circuit, a drug to be delivered to a patient to treat a medical condition, etc.).
  • the syringe 40 may include a fluid reservoir portion 44 to hold a fluid to be delivered and a coupling portion 48 that is fixedly mountable to the housing 55 .
  • Any suitable manner of affixing the coupling portion 48 and/or one or more other non-movable portions of the syringe 40 to the housing 55 may be used.
  • the fixing of the coupling portion 48 to the housing 55 may be provided with use of a syringe clamping or retaining structure 49 allowing the syringe to be affixed to housing 55 and later removed (e.g., the syringe being disposable, re-usable, capable of being sterilized, etc.).
  • the syringe 40 includes a plunger 46 .
  • the plunger 46 may include a first end positionable (e.g., movable) within the fluid reservoir portion 44 and a second end 47 .
  • the plunger 46 may be moved within the fluid reservoir portion 44 to provide a fluid flow to a connected line 42 (e.g., a line for infusion of anticoagulant which terminates in an arterial line).
  • the infusion apparatus 36 may further include an actuator 50 to control movement of the plunger 46 of the syringe 40 .
  • the actuator 50 may be any suitable actuator capable of controlling movement of the plunger 46 .
  • the actuator 50 may be a linear actuator that includes a mobile portion 56 (e.g., movable along a straight movement direction).
  • the mobile portion 56 may include a pushing structure 58 to interact with (e.g., have contact with or be coupled to) the plunger 46 (e.g., at the plunger end 47 ) to exert a pushing pressure thereon as the mobile portion 56 is moved for causing infusion of fluid from the fluid reservoir portion 44 into line 42 .
  • the mobile portion 56 of the actuator 50 may be guided by an endless screw translator 54 rotated by an electric motor 52 , for example, a step motor, to move the mobile portion 56 , and as such the pushing structure 58 , to apply the push force on the plunger 46 .
  • the motor 52 and the syringe retaining structure 49 are generally fixed to the same structure such that movement of the mobile portion 56 (e.g., truck) and pushing structure 58 (e.g., structure that may include a plunger clip 59 configured to capture the plunger end 47 ) may suitably move plunger 46 .
  • the infusion apparatus 36 may further comprise a force sensor 60 to measure a push force applied on the pushing structure 58 .
  • a force sensor may be used, such as, for example, one or more load cells, strain gauges, piezoelectric force sensor, torque controlled driving motor, etc.
  • the force sensor 60 may include an analog transducer of force (e.g., a load cell) which may continuously measure the pushing force applied on the pushing structure 58 .
  • Such a measured force may be an indirect measurement of the pressure of the fluid being infused.
  • the force sensor 60 may be arranged between the linearly moveable mobile portion 56 and the pushing structure 58 (e.g., structure in contact with plunger 46 ). In other words, the force sensor 60 enables a measurement to be taken of the force applied on the plunger 46 of the syringe 40 .
  • the infusion apparatus 36 may include other sensors, such as sensor for measuring the displacement of the mobile portion 56 of the linear actuator (e.g., including the pushing structure 58 ) so as to determine the distance over which the drive system or actuator moves the structure that moves the plunger (e.g., which may include a plunger clip that is configured to capture the plunger), may include various types of coupling structures (e.g., holding structures, clamping structures, etc.) to provide the coupling of the various components, etc.
  • sensors such as sensor for measuring the displacement of the mobile portion 56 of the linear actuator (e.g., including the pushing structure 58 ) so as to determine the distance over which the drive system or actuator moves the structure that moves the plunger (e.g., which may include a plunger clip that is configured to capture the plunger)
  • various types of coupling structures e.g., holding structures, clamping structures, etc.
  • the controller 14 may include any controller suitable to implement the functionality described herein, including the detection of abnormalities or occlusion of a fluid flow delivered by infusion apparatus 12 .
  • the controller 14 commands the infusion apparatus 12 to deliver a fluid flow into line 13 (e.g., commands the actuator 50 of the infusion apparatus 36 to deliver fluid into line 42 as shown in FIG. 2 ).
  • such control may be implemented as a function of one or more signals from the infusion apparatus 12 (e.g., signals provided by the force sensor 60 and a displacement sensor of the actuator 50 shown in FIG. 2 ).
  • the controller 14 operatively coupled to the infusion apparatus 12 may be any hardware/software architecture configured to provide the desired functionality.
  • the controller may include circuitry for sampling the force sensor, processing apparatus and associated software for processing data (e.g., signals representative of force or pressure measurements to implement the monitoring and/or detection algorithms described herein), output circuitry to generate control signals for use in controlling infusion fluid flow rates or for controlling one or more alarms, etc.
  • processing data e.g., signals representative of force or pressure measurements to implement the monitoring and/or detection algorithms described herein
  • output circuitry to generate control signals for use in controlling infusion fluid flow rates or for controlling one or more alarms, etc.
  • such controller functionality may be carried out by the apparatus 360 described therein.
  • Such processing apparatus may be, for example, any fixed or mobile computer system (e.g., a personal computer or mini-computer associated with, for example, a fluid treatment or processing system, such as a dialysis system).
  • the exact configuration of the computing apparatus is not limiting and essentially any device capable of providing suitable computing capabilities and control capabilities (e.g., control of the infusion apparatus 12 , monitoring of the force sensor signals to detect occlusions, etc.) may be used.
  • various peripheral devices such as a computer display, mouse, keyboard, memory, printer, scanner, are contemplated to be used in combination with processing apparatus, and its associated data storage.
  • data storage may allow for access to processing programs or routines and one or more other types of data that may be employed to carry out the illustrative methods and functionality as described herein.
  • the methods or systems described herein may be implemented using one or more computer programs or processes (or systems including such processes or programs) executed on programmable computers, such as computers that include, for example, processing capabilities, data storage (e.g., volatile or non-volatile memory and/or storage elements), input devices, and output devices.
  • programmable computers such as computers that include, for example, processing capabilities, data storage (e.g., volatile or non-volatile memory and/or storage elements), input devices, and output devices.
  • Program code and/or logic described herein may be applied to input data to perform functionality described herein and generate desired output information.
  • the output information may be applied as input to one or more other devices and/or processes as described herein or as would be applied in a known fashion.
  • processing programs or routines may include programs or routines for performing various algorithms, including standardization algorithms, comparison algorithms, or any other processing required to implement one or more embodiments described herein, such as those for performing analysis of measurement data, generation of control signals, etc.
  • Software or programs used to implement the functionality described herein may be provided using any programmable language, e.g., a high level procedural and/or object orientated programming language that is suitable for communicating with a processing apparatus. Any such programs may, for example, be stored on any suitable device, e.g., a storage media, readable by a general or special purpose program, computer or a processor apparatus for configuring and operating the computer when the suitable device is read for performing the procedures described herein.
  • the methods and systems described herein may be implemented using a computer readable storage medium, configured with a computer program, where the storage medium so configured causes the processing apparatus to operate in a specific and predefined manner to perform functions described herein.
  • the infusion system 10 including the monitoring system 20 may be used in any fluid processing systems that would benefit therefrom.
  • exemplary systems that may benefit from such occlusion detection may include systems, generally referred to as dialysis systems.
  • the general term dialysis as used herein includes hemodialysis, hemofiltration, hemodiafiltration, and therapeutic plasma exchange (TPE), among other similar treatment procedures.
  • TPE therapeutic plasma exchange
  • dialysis generally, blood is taken out of the body and exposed to a treatment device to separate substances therefrom and/or to add substances thereto, and is then returned to the body.
  • TPE therapeutic plasma exchange
  • the exemplary extracorporeal blood treatment system 310 may include a blood tubing circuit 312 having first and second tubing segments 314 and 316 which are both connected to the vascular system of a patient 318 via access and return devices 317 and 319 , respectively.
  • Devices 317 and 319 may be cannulas, catheters, winged needles or the like as would be understood by one skilled in the art.
  • Tubing segments 314 and 316 are also connected to a filtration or processing unit 320 .
  • filtration unit 320 is a dialyzer, which is also often referred to as a filter.
  • TPE it may also be referred to as a plasma filter.
  • a peristaltic pump 324 is disposed in operative association with the first tubing segment 314 .
  • Numerous other component devices of blood circuit 312 are also included, such as, for example, pressure sensors, tube clamps, etc.
  • FIG. 6 Also shown in FIG. 6 is the processing fluid or filtrate side of system 310 which generally includes a processing fluid circuit 340 having first and second processing fluid tubing segments 341 and 342 . Each of these tubing segments is connected to the filtration unit 320 . In FIG. 6 , a respective fluid pump 344 , 346 is operatively associated with each of these tubing segments 341 and 342 .
  • First tubing segment 341 is also connected to a processing fluid source (e.g., fluid bag 349 ) which may include electrolytes pre-mixed therein.
  • Second tubing segment 342 is connected to a waste collection device (e.g., a waste container such as a bag 353 ).
  • FIG. 6 shows a system which is common as a basic model for numerous dialysis procedures. Additional fluid lines, circuits, and components may be added (or deleted) to increase treatment options. Further, as shown in FIG. 6 , the system 310 includes an extracorporeal blood dialysis control apparatus 360 which provides numerous treatment options which are controlled and/or monitored via the control/display screen 361 (e.g., a control apparatus or controller provided in a system housing 393 ). Touch-screen controls may be incorporated herewith and/or other conventional knobs or buttons (not shown) may be used. Other and more detailed information regarding an example apparatus 360 may be found in U.S. Pat. No. 5,679,245; U.S. Pat. No. 5,762,805; U.S. Pat. No. 5,776,345; and U.S. Pat. No. 5,910,252; inter alia.
  • U.S. Pat. No. 5,679,245 U.S. Pat. No. 5,762,805; U.S. Pat. No
  • the system 310 shows an extracorporeal blood circuit 312 , provided with an arterial line and a venous line, as well as a circuit 340 for circulation of various treatment fluids that may include, according to the selected treatment, for example, a line supplying a dialysis fluid to the filter 320 and a discharge line for a used fluid exiting from the filter 320 .
  • the system 310 includes one or more infusion lines for various medical liquids (e.g., substitution liquids, anticoagulant, etc.).
  • an infusion apparatus including a syringe pump 364 (e.g., such as described herein or any other infusion apparatus) may be used to deliver anticoagulant through an anticoagulant line 365 to the extracorporeal blood circuit 312 .
  • the infusion apparatus may be suitable for administering liquids at low flow-rates.
  • a general dialysis treatment procedure as performed, for example, with an apparatus described with reference to FIG. 6 , will be generally described for exemplary purposes only.
  • blood is removed from the patient 318 via access device 317 and flows through access line 314 to the filter 320 .
  • infusion of an anticoagulant e.g., heparin
  • infusion apparatus 364 e.g., generally into the arterial line, through an infusion line, for example, line 365 , with relatively low infusion flow rates.
  • Filter 320 processes this blood according to a selected one or more of a number of extracorporeal blood treatment protocols (e.g., selected and controlled via screen interface 361 of control apparatus 360 ) and then the processed or treated blood is returned to the patient 318 through return line 316 and return device 319 inserted in or otherwise connected to the vascular system of the patient 318 .
  • the blood flow path to and from the patient 318 which includes the access device 317 , the access line 314 , the filter 320 , as well as the return line 316 and return device 319 back to the patient, forms the extracorporeal blood flow circuit 312 .
  • the infusion apparatus 364 may include a force sensor 18 (e.g., as schematically shown in FIG. 1 ) to provide a force signal associated therewith.
  • the force sensor may be a load cell configured to provide an electrical signal which is sent to a controller, such as controller 14 shown in FIG. 1 (e.g., an electrical micro-processing unit in control apparatus 360 for analysis of the signals for use in occlusion detection as described herein), which may then process the signal for display, storage or use by software (or hardware) for calculations, or for carrying out any other functionality (e.g., to initiate an alarm based on detection of an occlusion).
  • controller 14 shown in FIG. 1 e.g., an electrical micro-processing unit in control apparatus 360 for analysis of the signals for use in occlusion detection as described herein
  • the same or different controller or processing unit of apparatus 360 may be used for processing signals from other components of the system 310 to control a treatment being provided.
  • the systems and apparatus described with reference to FIGS. 1-2 and 6 are configured to detect abnormalities in the fluid flow delivered by an infusion apparatus thereof (e.g., infusion apparatus 12 as shown in FIG. 1 , the infusion apparatus 36 as shown in FIG. 2 , and infusion apparatus 364 as shown in FIG. 6 ).
  • a controller thereof as described herein, is configured to acquire from a force sensor thereof, a signal which is indicative of a resistant force (e.g., which is effectively opposed to the pushing structure 58 advancement as shown and described with reference to FIG. 2 ) representative of the pressure of the fluid being infused.
  • the resistant force reaches an equilibrium condition, for example, when delivering a constant fluid flow (e.g., during infusion of a certain fluid flow of anticoagulant in an extracorporeal blood circuit) or when no fluid flow is being delivered (e.g., such as before the start of infusion of such an anticoagulant).
  • the resistant force is a function of many parameters depending on the configuration of the system, among which include the pressure of the fluid internally of the syringe, the cylinder section the plunger runs through, the type of syringe, the speed of advancement of the plunger, etc.
  • one or more algorithms may be used (e.g., activated for detecting abnormal infusion situations, such as, for detecting partial or total occlusion).
  • the force measured by the sensor 18 may be used to detect the presence of an obstacle to the plunger advancement, to detect presence of an obstacle to liquid delivery into the extracorporeal circuit, to detect an occlusion in the line or tube which connects the syringe with the extracorporeal blood circuit, and/or to detect other obstacles to infusion of the fluid (e.g., an anticoagulant liquid in the extracorporeal circuit).
  • the controller 14 may be programmed to signal the risk of danger present to the system for the analysis thereof and possible activation of an alarm (e.g., alarm 24 ).
  • FIG. 3 is block diagram illustrating an exemplary occlusion detection algorithm 100 for detecting abnormalities in delivery of a fluid by an infusion apparatus which may be implemented, for example, by the systems and apparatus described herein.
  • the graphical illustration of FIG. 4 e.g., an exemplary perturbed force response
  • FIG. 5 shall be described to provide various techniques for reducing inaccuracies due to noise in the processes described.
  • the occlusion detection method 100 may include providing or establishing a fluid flow (block 102 ) (e.g., a low flow rate of anticoagulant).
  • a fluid flow e.g., a low flow rate of anticoagulant.
  • a pushing force e.g., pushing force on a plunger of a syringe
  • a value which is considered to be stable e.g., an equilibrium force relating to normal operating conditions or an equilibrium condition.
  • the force F 1 as indicated by line 144 is representative of an equilibrium force during normal operating or equilibrium conditions).
  • the infusion apparatus e.g., a syringe pump 36 shown in FIG. 2
  • the infusion apparatus may be commanded to intermittently deliver a defined volume of fluid causing at least one perturbation in the fluid flow (block 104 ).
  • Each of the perturbations caused in the fluid flow results in a perturbed force response over time.
  • the perturbed force response may be measured over time using, for example, force sensor 18 such as illustrated in FIG. 1 (e.g., a load cell of the pushing structure 58 of the syringe pump shown in FIG. 2 ).
  • Each perturbation is typically a short term increase in the infusion rate of the fluid which in turn causes a momentary increase in the pressure in the fluid.
  • a minimum bolus size to be delivered per perturbation to enable occlusion detection (e.g., one every bolus).
  • the minimum bolus size may need to be large enough (e.g., the plunger 46 must be moved far enough, the plunger 46 must be compressed enough to get the plunger seals to move relative to the syringe barrel, the pressure must be increased in the syringe) to affect fluid movement.
  • Smaller bolus sizes e.g., smaller than minimum bolus sizes may be used, but may require further filtering of the area ratios over multiple boluses to prevent false positives.
  • Such a perturbed force response is graphically illustrated in FIG. 4 for a normal, as opposed to abnormal, infusion operation (e.g., with no partial or total occlusion present).
  • the perturbation force response generally starts at time t 0 , where the delivery of the additional volume of fluid causes a rapid increase in the force sensed (e.g., over and above the equilibrium force F 1 ). This is shown by graph line 142 from time t 0 to time t 1 where a maximum perturbation force F 2 is reached shortly after the perturbation of the fluid flow. Further, as shown in FIG.
  • a maximum perturbation force F 2 will also be reached shortly after perturbation of the fluid flow.
  • the rate of decay of the perturbation force response back to equilibrium will be different than in normal operation.
  • the rate of decay may be virtually nonexistent such that following the reaching of the maximum perturbation force F 2 at time t 1 , the perturbed force response will be substantially maintained at force F 2 generally coinciding with graph line 160 .
  • the rate of decay may be much slower than shown for the normal operation in FIG.
  • the differences in the perturbation force response for normal versus abnormal operation can be used as described herein to provide detection of occlusions in fluid flow.
  • a 1 the area 164 under the perturbation force response F(t) (e.g., representative of the additional force over equilibrium due to the perturbation)
  • a 2 The area 162 above the perturbation force response
  • a 1 ⁇ t1 t2 F ( t ) ⁇ F 1
  • a 2 ⁇ t1 t2 F 2 ⁇ F ( t ).
  • the measured perturbed force response may be used to determine the existence of an occlusion (e.g., partial or total occlusion).
  • an integrated perturbed force response value may be determined for a corresponding perturbation in the fluid flow using integration of the force signal over a perturbation time period (e.g., summation over a time period) (block 108 ).
  • the perturbation time period may be adjusted depending on the infusion apparatus characteristics (e.g., may be set longer if typical decay of F(t) in normal operation is slow).
  • the integrated perturbed force response value at least in one embodiment, may be representative of the additional force caused by the perturbation over and above the equilibrium force.
  • either area A 1 or area A 2 may be an integrated perturbed force response value representative of the additional force caused by the perturbation over and above the equilibrium force.
  • area A 1 is the actual additional force caused by the perturbation over the equilibrium force.
  • Area A 2 is representative of such additional force caused by the perturbation over the equilibrium force since area A 2 is bounded by maximum perturbation force F 2 and, therefore, as the additional force caused by the perturbation changes, area A 2 also changes (i.e., A 2 is representative of the additional force caused by the perturbation).
  • the method 100 may also provide a ratio between the integrated perturbed force response value and a normalizing value (block 110 ).
  • the integrated perturbed force response value and the normalizing value may take either the numerator or denominator position of such a ratio.
  • the normalizing value determined for inclusion in the ratio may be based at least on the maximum perturbation force (e.g., the maximum perturbation force 146 shown in FIG. 4 resulting from a perturbation in the fluid flow) (block 112 ).
  • the normalizing value determined for a corresponding perturbation in the fluid flow may be representative of an integration, taken over the perturbation time, of the maximum perturbation force relative to equilibrium force (e.g., the integration being initiated at the occurrence of the maximum perturbation force, such as, for example, at time t 1 as shown in FIG. 4 , and the extending through the perturbation time period ending at time t 2 ).
  • the area A 1 plus area A 2 may be a normalizing value determined for a corresponding perturbation.
  • the normalizing value determined for a corresponding perturbation in the fluid flow may be representative of an integration, taken over the perturbation time, of the maximum perturbation force relative to the perturbed force response (e.g., the integration being initiated at the occurrence of the maximum perturbation force, such as, for example, at time t 1 as shown in FIG. 4 , and the extending through the perturbation time period ending at time t 2 ).
  • the area A 2 as shown in FIG. 4 may be a normalizing value determined for a corresponding perturbation.
  • Such various ratios between the integrated perturbed force response value and a normalizing value (block 110 ) may be described using the graphically illustrated areas shown in FIG. 4 for a perturbed force response.
  • ratios based on areas associated with the perturbed force response may include:
  • threshold ratios that can be used (e.g., for comparison to ratios determined for a particular perturbation) may be determined taking into consideration the following:
  • a threshold ratio indicative of an occlusion associated with A 1 /A 2 may be 2.0; whereas, a threshold ratio indicative of an occlusion associated with A 1 /(A 1 +A 2 ) may be 0.2.
  • One of the benefits of using such unit less ratios (e.g., normalized) for determining the occlusion limit is the elimination of the requirement for force/pressure calibration during service.
  • the detection limits are without units and thus independent of the unit of calibration.
  • the force/pressure sensor could be calibrated once at the time of manufacturing and never require calibration again if the rate of drift and offset were acceptable over the life thereof but it is not necessary for the detection of occlusions.
  • the ratio between an integrated perturbed force response value and a normalizing value may be used to determine if fluid flow is occluded. For example, such a determination may be made by comparing the ratio (block 110 ) to a predetermined ratio (e.g., a threshold ratio) indicative of an occlusion.
  • a predetermined ratio e.g., a threshold ratio
  • the threshold ratio may be set at 2.0, and as such, for example, if an A 1 /A 2 ratio for a particular perturbation is greater than 2.0, then an occlusion may be indicated.
  • the threshold ratio may be set at about 0.2, and as such, for example, if an A 1 /(A 1 +A 2 ) ratio for a particular perturbation is greater than 0.2, then an occlusion may be indicated.
  • the integrated perturbed force response value may be determined by integrating the force signal over a perturbation time period (e.g., summation over time) (e.g., integrating the force signal over the time period t 1 to t 2 as shown in FIG.
  • the integrated perturbed force response value equivalent, for example, to area A 2 (which is also representative of such additional force caused by the perturbation over the equilibrium force since area A 2 is bounded by maximum perturbation force F 2 ) may be calculated by providing the integration value representative of area A 1 and, subtracting such area from an area equivalent to area (A 1 +A 2 ) (e.g., (A 1 +A 2 ) being calculable from (F 2 ⁇ F 1 ) accumulated over time t 1 to t 2 ).
  • the normalizing value equivalent to area A 1 plus area A 2 may be determined from (F 2 ⁇ F 1 ) being accumulated over time t 1 to t 2 , while the normalizing value equivalent to area A 2 may be calculated in the same manner as it may be calculated when used as an integrated perturbed force response value.
  • FIG. 5 shows a block diagram illustrating another exemplary occlusion detection algorithm 200 for use in detecting abnormalities in delivery of a fluid by an infusion apparatus which may be implemented by a system such as shown generally in FIG. 1 .
  • the occlusion detection process 200 includes providing a ratio (e.g., a ratio as described herein, such as, area ratio A 1 /(A 1 +A 2 )) corresponding to a perturbation in the fluid flow (block 202 ).
  • the ratio for that particular corresponding perturbation may be compared to a ratio threshold to determine whether an occlusion is indicated (block 204 ). If no occlusion is indicated, then ratios continue to be provided for subsequent perturbations as indicated by line 203 .
  • a ratio satisfies a threshold (block 204 ) such that an occlusion is indicated
  • a process is initiated such that the single ratio which satisfied a threshold is not just indicative of a momentary appearance of occlusivity without an actual true line occlusion being present.
  • the ratio satisfies the threshold (block 204 )
  • ratios corresponding to one or more subsequent perturbations are provided and compared to the ratio threshold to determine whether such subsequent perturbations also have corresponding ratios which indicate an occlusion (block 206 ).
  • a predetermined number of ratios which indicate an occlusion are present (e.g., a number of sequential occlusion indicating ratios exceed a predetermined limit, a number of occlusion indicating ratios out of a certain number of sequential ratios exceed a predetermined limit, etc.) (block 208 )
  • an occlusion is detected (block 210 ).
  • the process of detecting whether an occlusion is present may be restarted as indicated by line 209 . If no occlusion is detected (block 210 ), one or more various functionalities may be carried out depending upon system configuration.
  • an alarm may be issued (e.g., visual, audible, tactile, etc.) or an alarm signal may be forwarded for use in one or more other algorithms (e.g., monitoring algorithms, alarm algorithms, safety algorithms, etc.).
  • the filtering performed by block 208 e.g., the filtering of the area ratios so that a false positive is avoided
  • FIGS. 7-10 show various graphical illustrations for use in describing one of more exemplary embodiments of the implementation of one or more algorithms described herein.
  • area ratios are shown in the top portion of the illustration corresponding to perturbations in the fluid flow shown by perturbed force responses in the lower portion of the illustration.
  • area ratios typical of an occluded infusion line are shown in FIG.
  • a first perturbed force response 400 corresponding to a first perturbation results in an area ratio greater than three (3); and a second perturbed force response 402 corresponding to a second perturbation results in an area ratio of about five (5) (e.g., the force measured as a result of the second perturbation continues to increase from the first perturbed force response 400 due to the occlusion).
  • Subsequent perturbed force responses 404 due to further perturbations while the occlusion is present continue to result in greater forces being measured and area ratios continuing to be of about three (3).
  • the area ratio falls to about one (1) as shown in region 46 of FIG. 7 .
  • area ratios typical of an un-occluded infusion line are shown in FIG. 8 (e.g., the change in area ratios A 1 /(A 1 +A 2 ) over time are shown for a 50 ml syringe (such as available from Terumo) based on perturbed force responses measured; the perturbed force responses caused by the delivery of 0.05 ml boluses are measured; and the integration for determining the area ratios is provided over a perturbation time period of 30 seconds).
  • each of the perturbed force responses 420 corresponding to a perturbation results in an area ratios less than 0.5.
  • area ratios of an un-occluded infusion line are shown in FIG. 9 (e.g., the change in area ratios A 1 /(A 1 +A 2 ) over time are shown for a 50 ml syringe (such as available from Terumo) based on perturbed force responses measured; the perturbed force responses caused by the delivery of 0.135 ml boluses are measured; and the integration for determining the area ratios is provided over a perturbation time period of 30 seconds).
  • the use of the larger bolus caused a first perturbed force response 430 resulting in an area ratio greater than four (4) which may be indicative of an occlusion.
  • the subsequent perturbed force responses 432 due to further perturbations indicated a lack of occlusion and area ratios being less than one (1).
  • area ratios typical of an un-occluded infusion line are shown in FIG. 10 (e.g., the change in area ratios A 1 /(A 1 +A 2 ) over time are shown for a 20 mL syringe (such as available from B-D Plastipak) based on perturbed force responses measured; the perturbed force responses caused by the delivery of 0.05 mL boluses are measured; and the integration for determining the area ratios is provided over a perturbation time period of 30 seconds).
  • the operating pressure of the infusion set point changes at approximately 625 seconds.
  • each of a first set of perturbed force responses 440 corresponding to a first set of perturbations results in area ratios less than 0.5 indicative of the lack of occlusion; however, upon occurrence of the first of a second set of perturbed force responses 450 corresponding to a second set of perturbations, an area ratio of about 2.5 occurs which may be indicative of an occlusion.
  • This larger area ratio occurs due to the change in the operating set point pressure at this point in time (e.g., at approximately 625 seconds) rather than being indicative of a true occlusion.
  • the following subsequent perturbed force responses 450 after the initial force response result in area ratios which are not indicative of an occlusion even though the flow set point was changed.

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Cited By (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US11406565B2 (en) 2015-03-10 2022-08-09 Regeneran Pharmaceuticals, Inc. Aseptic piercing system and method
US11547801B2 (en) 2017-05-05 2023-01-10 Regeneron Pharmaceuticals, Inc. Auto-injector
USD1007676S1 (en) 2021-11-16 2023-12-12 Regeneron Pharmaceuticals, Inc. Wearable autoinjector

Families Citing this family (9)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US10065003B2 (en) * 2012-12-28 2018-09-04 Gambro Lundia Ab Syringe pump engagement detection apparatus and methods
ES2743487T3 (es) 2015-04-15 2020-02-19 Gambro Lundia Ab Sistema de tratamiento con cebado por presión del aparato de infusión
US11512277B2 (en) * 2015-12-22 2022-11-29 Global Life Sciences Solutions Usa Llc Instruments for processing cells
US10953153B2 (en) 2016-06-01 2021-03-23 Fresenius Vial Sas Infusion device and method allowing for detecting a drift in a sensor signal
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Citations (45)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4534756A (en) 1983-04-11 1985-08-13 Ivac Corporation Fault detection apparatus and method for parenteral infusion system
US4710163A (en) 1986-06-06 1987-12-01 Ivac Corporation Detection of fluid flow faults in the parenteral administration of fluids
US4767406A (en) 1985-10-11 1988-08-30 Vickers Plc. Syringe pumps
US4846792A (en) 1988-03-08 1989-07-11 Baxter International Inc. Automatic infiltration detection system and method
US4898576A (en) 1986-06-06 1990-02-06 Philip James H Intravenous fluid flow monitor
EP0361793A2 (en) 1988-09-26 1990-04-04 Baxter International Inc. An In-Line infiltration detection apparatus and method
US4979940A (en) 1988-03-08 1990-12-25 Baxter International Inc. Infusion system, methodology, and algorithm for identifying patient-induced pressure artifacts
US5242408A (en) 1992-09-23 1993-09-07 Becton, Dickinson And Company Method and apparatus for determining pressure and detecting occlusions in a syringe pump
US5295967A (en) 1992-09-23 1994-03-22 Becton, Dickinson And Company Syringe pump having continuous pressure monitoring and display
US5356378A (en) 1992-01-22 1994-10-18 Ivac Corporation Fluid line condition detection
US5423743A (en) 1993-09-17 1995-06-13 Ivac Corporation Cannula position detection
WO1996008288A1 (en) 1994-09-13 1996-03-21 Ivac Medical Systems, Inc. Impedance monitoring system
US5647853A (en) 1995-03-03 1997-07-15 Minimed Inc. Rapid response occlusion detector for a medication infusion pump
US5679245A (en) 1993-02-12 1997-10-21 Cobe Laboratories, Inc. Retention device for extracorporeal treatment apparatus
US5695473A (en) 1994-07-27 1997-12-09 Sims Deltec, Inc. Occlusion detection system for an infusion pump
US5803712A (en) 1988-05-17 1998-09-08 Patient Solutions, Inc. Method of measuring an occlusion in an infusion device with disposable elements
US6065941A (en) 1998-07-01 2000-05-23 Deka Products Limited Partnership System for measuring when fluid has stopped flowing within a line
US6193480B1 (en) 1998-08-03 2001-02-27 Alaris Medical Systems, Inc. System and method for increased flow uniformity
US6213972B1 (en) 1994-09-13 2001-04-10 Alaris Medical Systems, Inc. Fluid flow resistance monitoring system
US6416291B1 (en) 1996-07-30 2002-07-09 Alaris Medical Systems, Inc. Fluid flow resistance monitoring system
US6485465B2 (en) 2000-03-29 2002-11-26 Medtronic Minimed, Inc. Methods, apparatuses, and uses for infusion pump fluid pressure and force detection
US6572604B1 (en) 2000-11-07 2003-06-03 Baxter International Inc. Occlusion detection method and system for ambulatory drug infusion pump
US20040133166A1 (en) 2002-11-22 2004-07-08 Minimed Inc. Methods, apparatuses, and uses for infusion pump fluid pressure and force detection
WO2004057196A1 (en) 2002-12-19 2004-07-08 Pursuit Dynamics Plc A pumping system
EP1529546A1 (en) 2003-11-04 2005-05-11 Medex, Inc. Syringe pump rapid occlusion detection system
US20050131331A1 (en) 2003-12-16 2005-06-16 Kelly Thomas D. Medical fluid therapy flow control systems and methods
EP1676527A1 (en) 2004-12-29 2006-07-05 Codman & Shurtleff, Inc. System and method for measuring the pressure of a fluid system within a patient
US20060184154A1 (en) 1998-10-29 2006-08-17 Medtronic Minimed, Inc. Methods and apparatuses for detecting occlusions in an ambulatory infusion pump
US7306736B2 (en) 2000-12-08 2007-12-11 Nephros, Inc. Valve mechanism for infusion fluid systems
WO2007141786A1 (en) 2006-06-08 2007-12-13 Medingo Ltd. System for detecting an occlusion in a tube
US20090012453A1 (en) 2007-07-05 2009-01-08 Baxter International Inc. Mobile dialysis system having supply container detection
US7517332B2 (en) 2004-04-20 2009-04-14 Gambro Lundia Ab Infusion device for medical fluids
EP2052683A1 (en) 2007-10-23 2009-04-29 Sensile Pat AG Liquid flow sensing system
US20100069841A1 (en) 2003-10-02 2010-03-18 Medtronic, Inc. Determining catheter status
WO2010046728A1 (en) 2008-10-22 2010-04-29 Debiotech S.A. Mems fluid pump with integrated pressure sensor for dysfunction detection
US7867192B2 (en) 2008-02-29 2011-01-11 The Alfred E. Mann Foundation For Scientific Research Ambulatory infusion devices and methods with blockage detection
EP2305334A2 (en) 2003-12-31 2011-04-06 CareFusion 303, Inc. Medication safety enhancement for secondary infusion
US8109906B2 (en) 2005-03-17 2012-02-07 Smisson-Cartledge Biomedical Llc Control of a pump device
US8267881B2 (en) 2000-11-02 2012-09-18 Gambro Uf Solutions, Inc. Method and apparatus for blood withdrawal and infusion using a pressure controller
WO2012151077A2 (en) 2011-05-05 2012-11-08 Carefusion 303, Inc. Fluid infusion method and apparatus
WO2013004307A1 (en) 2011-07-06 2013-01-10 F. Hoffmann-La Roche Ag Device and method for automatic injection and occlusion detection
US20140188076A1 (en) 2011-12-21 2014-07-03 Deka Products Limited Partnership Syringe Pump, and Related Method and System
US20140194820A1 (en) 1999-07-20 2014-07-10 Deka Products Limited Partnership Fluid pumping apparatus for use with a removable fluid pumping cartridge
US20140236119A1 (en) * 2013-02-15 2014-08-21 Micrel Medical Devices S.A. Method for Processing Infusion Data and an Infusion Pump System
US20150005732A1 (en) * 2013-06-26 2015-01-01 Carefusion 303, Inc. Fluid line occlusion detection system and methods

Family Cites Families (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5087245A (en) 1989-03-13 1992-02-11 Ivac Corporation System and method for detecting abnormalities in intravascular infusion

Patent Citations (57)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4534756A (en) 1983-04-11 1985-08-13 Ivac Corporation Fault detection apparatus and method for parenteral infusion system
US4767406A (en) 1985-10-11 1988-08-30 Vickers Plc. Syringe pumps
US4710163A (en) 1986-06-06 1987-12-01 Ivac Corporation Detection of fluid flow faults in the parenteral administration of fluids
US4898576A (en) 1986-06-06 1990-02-06 Philip James H Intravenous fluid flow monitor
US4846792A (en) 1988-03-08 1989-07-11 Baxter International Inc. Automatic infiltration detection system and method
US4979940A (en) 1988-03-08 1990-12-25 Baxter International Inc. Infusion system, methodology, and algorithm for identifying patient-induced pressure artifacts
US5803712A (en) 1988-05-17 1998-09-08 Patient Solutions, Inc. Method of measuring an occlusion in an infusion device with disposable elements
EP0361793A2 (en) 1988-09-26 1990-04-04 Baxter International Inc. An In-Line infiltration detection apparatus and method
US4959050A (en) 1988-09-26 1990-09-25 Baxter International Inc. In-line infiltration detection apparatus and method
WO1991000113A2 (en) 1989-06-22 1991-01-10 Baxter International Inc. Infusion system, methodology, and algorithm for identifying patient-induced pressure artifacts
US5356378A (en) 1992-01-22 1994-10-18 Ivac Corporation Fluid line condition detection
US5295967A (en) 1992-09-23 1994-03-22 Becton, Dickinson And Company Syringe pump having continuous pressure monitoring and display
US5242408A (en) 1992-09-23 1993-09-07 Becton, Dickinson And Company Method and apparatus for determining pressure and detecting occlusions in a syringe pump
US5910252A (en) 1993-02-12 1999-06-08 Cobe Laboratories, Inc. Technique for extracorporeal treatment of blood
US5679245A (en) 1993-02-12 1997-10-21 Cobe Laboratories, Inc. Retention device for extracorporeal treatment apparatus
US5776345A (en) 1993-02-12 1998-07-07 Cobe Laboratories, Inc. Automatic priming technique
US5762805A (en) 1993-02-12 1998-06-09 Cobe Laboratories, Inc. Technique for extracorporeal treatment of blood
US5423743A (en) 1993-09-17 1995-06-13 Ivac Corporation Cannula position detection
US5695473A (en) 1994-07-27 1997-12-09 Sims Deltec, Inc. Occlusion detection system for an infusion pump
WO1996008288A1 (en) 1994-09-13 1996-03-21 Ivac Medical Systems, Inc. Impedance monitoring system
US6213972B1 (en) 1994-09-13 2001-04-10 Alaris Medical Systems, Inc. Fluid flow resistance monitoring system
US5647853A (en) 1995-03-03 1997-07-15 Minimed Inc. Rapid response occlusion detector for a medication infusion pump
US6416291B1 (en) 1996-07-30 2002-07-09 Alaris Medical Systems, Inc. Fluid flow resistance monitoring system
US6065941A (en) 1998-07-01 2000-05-23 Deka Products Limited Partnership System for measuring when fluid has stopped flowing within a line
US6193480B1 (en) 1998-08-03 2001-02-27 Alaris Medical Systems, Inc. System and method for increased flow uniformity
US20060184154A1 (en) 1998-10-29 2006-08-17 Medtronic Minimed, Inc. Methods and apparatuses for detecting occlusions in an ambulatory infusion pump
US7998111B2 (en) 1998-10-29 2011-08-16 Medtronic Minimed, Inc. Methods and apparatuses for detecting occlusions in an ambulatory infusion pump
US20140194820A1 (en) 1999-07-20 2014-07-10 Deka Products Limited Partnership Fluid pumping apparatus for use with a removable fluid pumping cartridge
US6485465B2 (en) 2000-03-29 2002-11-26 Medtronic Minimed, Inc. Methods, apparatuses, and uses for infusion pump fluid pressure and force detection
US8267881B2 (en) 2000-11-02 2012-09-18 Gambro Uf Solutions, Inc. Method and apparatus for blood withdrawal and infusion using a pressure controller
US6572604B1 (en) 2000-11-07 2003-06-03 Baxter International Inc. Occlusion detection method and system for ambulatory drug infusion pump
US6648861B2 (en) 2000-11-07 2003-11-18 Baxter International Inc. Occlusion detection method and system for ambulatory drug infusion pump
US7306736B2 (en) 2000-12-08 2007-12-11 Nephros, Inc. Valve mechanism for infusion fluid systems
US20040133166A1 (en) 2002-11-22 2004-07-08 Minimed Inc. Methods, apparatuses, and uses for infusion pump fluid pressure and force detection
WO2004057196A1 (en) 2002-12-19 2004-07-08 Pursuit Dynamics Plc A pumping system
US20100069841A1 (en) 2003-10-02 2010-03-18 Medtronic, Inc. Determining catheter status
US8182461B2 (en) 2003-11-04 2012-05-22 Smiths Medical Asd, Inc. Syringe pump rapid occlusion detection system
US20140058351A1 (en) 2003-11-04 2014-02-27 Smiths Medical Asd, Inc. Syringe pump rapid occlusion detection system
US20120245525A1 (en) 2003-11-04 2012-09-27 Smiths Medical Asd, Inc. Syringe pump rapid occlusion detection system
EP1529546A1 (en) 2003-11-04 2005-05-11 Medex, Inc. Syringe pump rapid occlusion detection system
US20120203195A1 (en) 2003-11-04 2012-08-09 Smiths Medical Asd, Inc. Syringe pump rapid occlusion detection system
US20050131331A1 (en) 2003-12-16 2005-06-16 Kelly Thomas D. Medical fluid therapy flow control systems and methods
EP2305334A2 (en) 2003-12-31 2011-04-06 CareFusion 303, Inc. Medication safety enhancement for secondary infusion
US7517332B2 (en) 2004-04-20 2009-04-14 Gambro Lundia Ab Infusion device for medical fluids
EP1676527A1 (en) 2004-12-29 2006-07-05 Codman & Shurtleff, Inc. System and method for measuring the pressure of a fluid system within a patient
US8109906B2 (en) 2005-03-17 2012-02-07 Smisson-Cartledge Biomedical Llc Control of a pump device
US8764408B2 (en) 2005-03-17 2014-07-01 Smisson-Cartledge Biomedical Llc User interface and controls for a pump device
WO2007141786A1 (en) 2006-06-08 2007-12-13 Medingo Ltd. System for detecting an occlusion in a tube
US20090012453A1 (en) 2007-07-05 2009-01-08 Baxter International Inc. Mobile dialysis system having supply container detection
EP2052683A1 (en) 2007-10-23 2009-04-29 Sensile Pat AG Liquid flow sensing system
US7867192B2 (en) 2008-02-29 2011-01-11 The Alfred E. Mann Foundation For Scientific Research Ambulatory infusion devices and methods with blockage detection
WO2010046728A1 (en) 2008-10-22 2010-04-29 Debiotech S.A. Mems fluid pump with integrated pressure sensor for dysfunction detection
WO2012151077A2 (en) 2011-05-05 2012-11-08 Carefusion 303, Inc. Fluid infusion method and apparatus
WO2013004307A1 (en) 2011-07-06 2013-01-10 F. Hoffmann-La Roche Ag Device and method for automatic injection and occlusion detection
US20140188076A1 (en) 2011-12-21 2014-07-03 Deka Products Limited Partnership Syringe Pump, and Related Method and System
US20140236119A1 (en) * 2013-02-15 2014-08-21 Micrel Medical Devices S.A. Method for Processing Infusion Data and an Infusion Pump System
US20150005732A1 (en) * 2013-06-26 2015-01-01 Carefusion 303, Inc. Fluid line occlusion detection system and methods

Non-Patent Citations (2)

* Cited by examiner, † Cited by third party
Title
International Preliminary Report on Patentability for PCT/US2013/076400 dated Jul. 9, 2015 (14 pages).
International Search Report and Written Opinion for PCT/US2013/076400 dated Mar. 27, 2014 (16 pages).

Cited By (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US11406565B2 (en) 2015-03-10 2022-08-09 Regeneran Pharmaceuticals, Inc. Aseptic piercing system and method
US11547801B2 (en) 2017-05-05 2023-01-10 Regeneron Pharmaceuticals, Inc. Auto-injector
USD1007676S1 (en) 2021-11-16 2023-12-12 Regeneron Pharmaceuticals, Inc. Wearable autoinjector

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